Automatically pulsing different aspiration levels to an ocular probe

ABSTRACT

Methods and systems for automatically pulsing different aspiration levels to an ocular probe are disclosed. The probe may be a phacoemulsification probe. A first aspiration level, supplied by a first pump, may be applied to the probe simultaneously with ultrasonic energy. A second aspiration level, supplied by a second pump, may be automatically switched from the first aspiration level, and applied to the probe in a pulsed manner.

This application is claims priority to and is a divisional of U.S. application Ser. No. 12/614,013, filed Nov. 6, 2009, which claims priority to U.S. Application No. 61/198,658, filed on Nov. 7, 2008, the entirety of which are hereby incorporated by reference.

FIELD OF THE INVENTION

The present invention relates generally to the field of surgery, and more specifically to devices, systems, and methods for treatment of an eye. Exemplary embodiments allow enhanced treatment to structures within an eye by at least once (though more commonly repeatedly or even cyclically) applying different levels and/or types of aspiration to an ocular probe, often such that the aspiration changes during a treatment of a particular eye.

BACKGROUND OF THE INVENTION

The present invention is generally related to methods, devices, and systems for controlling surgical fluid flows, particularly during treatment of an eye. In exemplary embodiments, the invention removes material from within the eye in part by a displacement-induced aspiration flow (such as that caused by a peristaltic or other positive displacement pump), and in part by a vacuum-induced aspiration flow (such as that caused by a venturi pump). Optionally, the aspiration flow may switch between a displacement pump and a venturi pump while material is being fragmented and removed from within the eye. While the system operator will typically have control over the overall mode of operation throughout a procedure, switching between these two different types of aspiration flow may occur “on-the-fly” without halting of a corresponding irrigation flow, and without awaiting input from the system operator regarding that particular flow change. The material may be removed from an anterior or posterior chamber of the eye, such as for phacoemulsification of cataracts, treatment of retinal diseases, vitrectomy, and the like.

The optical elements of the eye include both a cornea (at the front of the eye) and a lens within the eye. The lens and cornea work together to focus light onto the retina at the back of the eye. The lens also changes in shape, adjusting the focus of the eye to vary between viewing near objects and far objects. The lens is found just behind the pupil, and within a capsular bag. This capsular bag is a thin, relatively delicate structure which separates the eye into anterior and posterior chambers.

With age, clouding of the lens or cataracts is fairly common. Cataracts may form in the hard central nucleus of the lens, in the softer peripheral cortical portion of the lens, or at the back of the lens near the capsular bag.

Cataracts can be treated by the replacement of the cloudy lens with an artificial lens. Phacoemulsification systems often use ultrasound energy to fragment the lens and aspirate the lens material from within the capsular bag. This may allow the remaining capsular bag to be used for positioning of the artificial lens, and maintains the separation between the anterior portion of the eye and the vitreous humour in the posterior chamber of the eye.

During cataract surgery and other therapies of the eye, accurate control over the volume of fluid within the eye is highly beneficial. For example, while ultrasound energy breaks up the lens and allows it to be drawn into a treatment probe with an aspiration flow, a corresponding irrigation flow may be introduced into the eye so that the total volume of fluid in the eye does not change excessively. If the total volume of fluid in the eye is allowed to get too low at any time during the procedure, the eye may collapse and cause significant tissue damage. Similarly, excessive pressure within the eye may strain and injure tissues of the eye.

While a variety of specific fluid transport mechanisms have been used in phacoemulsification and other treatment systems for the eyes, aspiration flow systems can generally be classified in two categories: 1) volumetric-based aspiration flow systems using positive displacement pumps; and 2) vacuum-based aspiration systems using a vacuum source, typically applied to the aspiration flow through an air-liquid interface. Among positive displacement aspiration systems, peristaltic pumps (which use rotating rollers that press against a flexible tubing to induce flow) are commonly employed. Such pumps provide accurate control over the flow volume. The pressure of the flow, however, is less accurately controlled and the variations in vacuum may result in the feel or traction of the handpiece varying during a procedure. Peristaltic and other displacement pump systems may also be somewhat slow for some procedures. Vacuum rise times tend to be slower for peristaltic systems than venturi systems. This may result in an overall sluggish feel to the surgeon. Moreover, the ultrasonic vibrations of a phacoemulsification tip may (despite peristaltic aspiration flow into the tip) inhibit the desired fragmentation-inducing engagement between the tip and tissue particles.

Vacuum-based aspiration systems provide accurate control over the fluid pressure within the eye, particularly when combined with gravity-fed irrigation systems. While vacuum-based systems can (in some circumstances) result in excessive fluid flows, they may have advantages when, for example, it is desired to bring tissue fragments to the probe, or when removing a relatively large quantity of the viscous vitreous humour from the posterior chamber of the eye. Unfortunately, venturi pump and other vacuum-based aspiration flow systems are subject to pressure surges during occlusion of the treatment probe, and such pressure surges may decrease the surgeon's control over the eye treatment procedure. Displacement pump systems are similarly subject to vacuum spikes during and immediately following occlusion of the probe.

While there have been prior proposals for multiple pump systems which make use of either a positive displacement pump or a vacuum source, the previously proposed systems have not been ideal. Hence, to provide surgeons with the benefits of both vacuum-based and displacement-based aspiration flows, still further improvements appear desirable. In particular, interrupting a procedure to switch between aspiration systems may be inconvenient, and it may be difficult or even impossible to take full advantage (for example) of the full potential of combining both vacuum-based and displacement-based aspiration flows using prior eye treatment systems.

In light of the above, it would be advantageous to provide improved devices, systems, and methods for eye surgery. It would be particularly advantageous if these improvements allowed system users to maintain the benefits of vacuum and/or displacement fluid control systems when appropriate, and without having to interrupt the procedure to manually switch pumps, change hand pieces or other system components, or the like. Ideally, these improved systems would provide benefits beyond those of peristaltic or venturi systems alone, or combination peristaltic/venturi systems, without delaying the procedure or increasing the complexity of the operation to the system operator.

BRIEF SUMMARY OF THE INVENTION

One embodiment of the invention may include a method for applying aspiration to a probe, which may be computer implemented. The method may include applying a low flow-rate aspiration from a first pump to an aspiration port of a probe, detecting that the aspiration port is insufficiently occluded, applying a high flow-rate aspiration from a second pump to the non-occluded aspiration port, detecting that the aspiration port is sufficiently occluded, and discontinuing the high flow-rate aspiration and reapplying the low flow-rate aspiration to the occluded aspiration port. Any of the steps of the method may automatically occur based on the program being used.

Another embodiment of the invention may include a method for removing tissue from within an eye. The method may include aspirating fluid and material using a probe within the eye by pumping the fluid and material through an aspiration pathway with a first pump (e.g. a volumetric pump or a pressure pump), generating a command signal by detecting insufficient occlusion of the aspiration pathway during the first pumping, bringing material from within the eye to the probe by a second pump in response to the command signal, and resuming aspiration of the material and the fluid with the first pump after the second pump. The first pump and the second pump may comprise a flow based pump and/or a vacuum based pump.

Yet another embodiment of the invention may include a system for removing tissue from within an eye. The system may include a probe having a distal tip insertable into the eye, wherein the tip comprises an aspiration port, a console coupled with/to the port along an aspiration pathway, and wherein the console comprises a processor and a pump system. Further, the pump system comprises a first pump and a second pump for providing a first aspiration rate and a second aspiration rate higher than the first pump rate, and the processor is configured to, during pumping of aspiration flow along the aspiration pathway at the first aspiration rate and in response to insufficient occlusion of the aspiration pathway, generate a command signal so as to induce pumping of the aspiration flow along the aspiration pathway at the second aspiration rate.

Yet another embodiment of the invention may include a method for applying aspiration to a phacoemulsification device. The method may be computer implemented. The method may include applying a first flow-rate (e.g. low flow-rate) aspiration from a first pump to an aspiration port of a phacoemulsification device, periodically applying ultrasonic energy to the phacoemulsification device according to a predetermined duty cycle, and applying a second flow-rate (e.g. high flow-rate) aspiration from a second pump to the aspiration port when ultrasonic energy is not being applied. Any of the steps of the method may automatically occur based on the program being used.

Yet another embodiment of the invention may include a phacoemulsification system. The system including a probe having a distal tip insertable into an eye, wherein the tip is energizable with phacoemulsification energy and comprises an aspiration port. The system further includes a console coupled with/to the port along an aspiration pathway, wherein the console comprises a processor and a pump system. The pump system comprises a first pump and a second pump for providing a first pump rate and a second pump rate higher than the first pump rate. Further, the processor is configured to, during pumping of aspiration flow along the aspiration pathway, transmit time coordinated command signals to energize the tip with the energy and switch between the pumping rates.

Yet another embodiment of the invention may include a method for applying aspiration to a probe device. The method may be computer implemented. The method may include applying a low flow-rate aspiration from a first pump to an aspiration port of a phacoemulsification device, detecting that the aspiration port is sufficiently occluded, and cycling a high flow-rate aspiration with a high-flow rate reflux from a second pump to the aspiration port.

Yet another embodiment of the invention may include a method for removing material from an eye. The method may include applying a first aspiration level to an aspiration port of a probe within an eye, applying a second aspiration level higher than the first aspiration level to the port, and cycling between the aspiration levels sufficiently for transient-induced effects of the aspiration level to help break-up the material for aspiration through the port.

Yet another embodiment of the invention may include a system for removing material from within an eye. The system may include a probe having a distal tip insertable into the eye, wherein the tip comprises an aspiration port, and a console coupled with/to the port along an aspiration pathway. The console comprises a processor and a pump system, wherein the pump system comprises a first pump and a second pump for providing a first aspiration level and a second aspiration level higher than the first aspiration level. Further, the processor is configured to cycle between the aspiration levels sufficiently for transient-induced effects of the aspiration level to help break-up the material for aspiration through the port.

Yet another embodiment of the invention may include a computer implemented method for applying aspiration through a probe. The method may include applying a low flow-rate aspiration from a first pump to an aspiration port of a probe, receiving a user input to change to a high flow-rate aspiration from a second pump to the aspiration port, and switching the low flow-rate aspiration to the high flow-rate aspiration in response to the user input.

To better understand the nature and advantages of the invention, reference should be made to the following description and the accompanying figures. It is to be understood, however, that the figures and descriptions of exemplary embodiments are provided for the purpose of illustration only and is not intended as a definition of the limits of the scope of the present invention.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 illustrates an exemplary phacoemulsification/vitrectomy irrigation/aspiration system in a functional block diagram to show the components and interfaces for a safety critical medical instrument system that may be employed in accordance with an embodiment of the present invention;

FIGS. 2A and 2B are a functional block diagrams of an exemplary surgical cassette venting systems, according to embodiments of the invention;

FIG. 3 is a functional block diagram illustrating a surgical cassette venting system configured for venting to a BSS (irrigation) bottle, according to one embodiment of the invention;

FIG. 4 is a functional block diagram illustrating a surgical cassette venting system configured for peristaltic aspiration operation, according to one embodiment of the invention;

FIG. 5 is a functional block diagram illustrating a surgical cassette venting system configured for peristaltic venting operation, according to one embodiment of the invention;

FIG. 6 is a functional block diagram illustrating a surgical cassette venting system configured for vacuum regulator aspiration operation, according to one embodiment of the invention;

FIG. 7 is a functional block diagram illustrating a surgical cassette venting system configured for vacuum regulator venting operation, according to one embodiment of the invention;

FIG. 8 is a graphical depiction of the operation of a surgical system, according to one embodiment of the invention;

FIG. 9A is a flow chart of a method for applying aspiration to a probe, according to one embodiment of the invention;

FIG. 9B is a graphical depiction of the operation of a surgical system, according to one embodiment of the invention;

FIG. 10A is a flow chart of a method for applying aspiration to a probe, according to one embodiment of the invention;

FIG. 10B is a graphical depiction of the operation of a surgical system, according to one embodiment of the invention;

FIG. 11A is a flow chart of a method for applying aspiration to a probe, according to one embodiment of the invention;

FIG. 11B is a graphical depiction of the operation of a surgical system, according to one embodiment of the invention; and

FIG. 12 is a flow chart of a method for applying aspiration to a probe, according to one embodiment of the invention.

DETAILED DESCRIPTION OF THE INVENTION

FIG. 1 illustrates an exemplary phacoemulsification/vitrectomy system 100 in a functional block diagram to show the components and interfaces for a safety critical medical instrument system that may be employed in accordance with an aspect of the present invention. A serial communication cable 103 connects GUI host 101 module and instrument host 102 module for the purposes of controlling the surgical instrument host 102 by the GUI host 101. GUI host 101 and instrument host 102, as well as any other component of system 100, may be connected wirelessly. Instrument host 102 may be considered a computational device in the arrangement shown, but other arrangements are possible. An interface communications cable 120 is connected to instrument host 102 module for distributing instrument sensor data 121, and may include distribution of instrument settings and parameters information, to other systems, subsystems and modules within and external to instrument host 102 module. Although shown connected to the instrument host 102 module, interface communications cable 120 may be connected or realized on any other subsystem (not shown) that could accommodate such an interface device able to distribute the respective data.

A switch module associated with foot pedal 104 may transmit control signals relating internal physical and virtual switch position information as input to the instrument host 102 over serial communications cable 105 (although foot pedal 104 may be connected wireless, e.g. Bluetooth, IR). Instrument host 102 may provide a database file system for storing configuration parameter values, programs, and other data saved in a storage device (not shown). In addition, the database file system may be realized on the GUI host 101 or any other subsystem (not shown) that could accommodate such a file system. The foot pedal system (104) can be configured as dual linear. In this configuration, the surgeon can dictate the system to operate with the peristaltic pump in the traditional pitch and add the venturi vacuum with the yaw mechanism. This will allow a surgeon the control of peristaltic operation with the added efficiency of venturi operation. The foot pedal 104 can also combine longitudinal cutting modes with a certain pump and non-longitudinal cutting modes (i.e., transversal, torsion, etc.) with a different pump for example, the foot pedal pitch could control a peristaltic pump with longitudinal ultrasonic cutting, and the yaw could control the venturi pump with non-longitudinal cutting. The foot pedal can also be configured to operate using a certain pump by yawing to the left and operate a second pump by yawing to the right. This gives the user the ability to switch-on-the-fly without accessing the user interface which may be timely and cumbersome.

The phacoemulsification/vitrectomy system 100 has a handpiece 110 that includes a needle and electrical means, typically a piezoelectric crystal, for ultrasonically vibrating the needle. The instrument host 102 supplies power on line 111 to a phacoemulsification/vitrectomy handpiece 110. An irrigation fluid source 112 can be fluidly coupled with/to handpiece 110 through line 113. The irrigation fluid and ultrasonic power are applied by handpiece 110 to an eye, or affected area or region, indicated diagrammatically by block 114. Alternatively, the irrigation source may be routed to eye 114 through a separate pathway independent of the handpiece. Aspiration is provided to eye 114 by one or more pumps (not shown), such as a peristaltic pump, via the instrument host 102, through lines 115 and 116. A surgeon/operator may select an amplitude of electrical pulses either using the handpiece, foot pedal, via the instrument host and/or GUI host, and/or by voice command.

The instrument host 102 generally comprises at least one processor board. Instrument host 102 may include many of the components of a personal computer, such as a data bus, a memory, input and/or output devices (including a touch screen (not shown)), and the like. Instrument host 102 will often include both hardware and software, with the software typically comprising machine readable code or programming instructions for implementing one, some, or all of the methods described herein. The code may be embodied by a tangible media such as a memory, a magnetic recording media, an optical recording media, or the like. A controller (not shown) may have (or be coupled with/to) a recording media reader, or the code may be transmitted to instrument host 102 by a network connection such as an internet, an intranet, an Ethernet, a wireless network, or the like. Along with programming code, instrument host 102 may include stored data for implementing the methods described herein, and may generate and/or store data that records parameters reflecting the treatment of one or more patients.

In combination with phacoemulsification system 100, the present system enables aspiration, venting, or reflux functionality in or with the phacoemulsification system and may comprise components including, but not limited to, a flow selector valve, two or more pumps, a reservoir, and a collector, such as a collection bag or a device having similar functionality. The collector in the present design collects aspirant from the ocular surgical procedure.

FIG. 2A illustrates an exemplary surgical cassette system in a functional block diagram that shows the components and interfaces that may be employed in accordance with an aspect of the present design. An irrigation source 46 of, and/or controlled by, instrument host 102 optionally provides irrigation fluid pressure control via an irrigation line 51 by relying at least in part on a gravity pressure head that varies with a height of an irrigation fluid bag or the like. An irrigation on/off pinch valve 48 may generally include a short segment of a flexible conduit of cassette 16A, which can be engaged and actuated by an actuator of the instrument host 102, with a surface of the cassette body often being disposed opposite the actuator to facilitate closure of the conduit lumen. Alternative irrigation flow systems may include positive displacement pumps, alternative fluid pressurization drive systems, fluid pressure or flow modulating valves, and/or the like.

In certain embodiments, irrigation fluid is alternatively or additionally provided to a separate handpiece (not shown). The aspiration flow network 50 generally provides an aspiration flow path 52 that can couple an aspiration port in the tip of handpiece 110 to either a peristaltic pump 54, formed by engagement of cassette 16A with instrument host 102, and/or a holding tank 56. Fluid aspirated through the handpiece 110 may be contained in holding tank 56 regardless of whether the aspiration flow is induced by peristaltic pump 54 or the vacuum applied to the holding tank 56 via pump 57. When pinch valve 58 is closed and peristaltic pump 54 is in operation, pumping of the aspiration flow may generally be directed by the peristaltic pump 54, independent of the pressure in the holding tank 56. Conversely, when peristaltic pump 54 is off, flow through the peristaltic pump may be halted by pinching of the elastomeric tubing arc of the peristaltic pump by one or more of the individual rollers of the peristaltic pump rotor. Hence, any aspiration fluid drawn into the aspiration network when peristaltic pump 54 is off will typically be effected by opening of a pinch valve 58 so that the aspiration port of the probe is in fluid communication with the holding tank. Regardless, the pressure within tank 56 may be maintained at a controlled vacuum level, often at a fixed vacuum level, by a vacuum system 59 of instrument host 102.

Vacuum system 59 may comprise a Venturi pump 57, a rotary vane pump, a vacuum source, a vent valve 44, a filter, and/or the like. Aspiration flow fluid that drains into holding tank 56 may be removed by a peristaltic drain pump 60 and directed to a disposal fluid collection bag 62. Vacuum pressure at the surgical handpiece 110 may be maintained within a desired range through control of the fluid level in the holding tank. In particular, peristaltic drain pump 60 enables the holding tank 56 to be drained including, while vacuum-based aspiration continues using vacuum system 59. In more detail, the operation of aspiration flow network 50 can be understood by first considering the flow when pinch valve 58 is closed. In this mode, peristaltic pump 54 draws fluid directly from handpiece 110, with a positive displacement peristaltic pump flow rate being controlled by a system controller. To determine the appropriate flow rate, the level of vacuum within the aspiration flow network may be identified in part with reference to a vacuum sensor 64 with three ports disposed along the aspiration flow network 50 between peristaltic pump 54, handpiece 110, and pinch valve 58. This allows the system to detect and adjust for temporary occlusions of the handpiece 110 and the like. Venting or reflux of the handpiece 110 in this state may be achieved by reversing the rotation of peristaltic pump 54 or by opening pinch valve 58 to equalize fluid pressures. Pinch valve 58 may be configured as a variable restrictor to regulate the amount of fluid that is vented and/or refluxed from the high pressure side of peristaltic pump 54 to the low pressure side. In this mode, while the aspiration material flows through holding tank 56 and eventually into collection bag 62, the holding tank pressure may have little or no effect on the flow rate. When peristaltic pump 54 is not in operation, rotation of the peristaltic pump is may be inhibited and the rotors of the peristaltic pump generally pinch the arcuate resilient tubing of the probe so as to block aspiration flow. Material may then be drawn into the aspiration port of handpiece 110 by opening pinch valve 58 and engagement or operation of the vacuum system 59. When pinch valve 58 is open, the aspiration port draws fluid therein based on the pressure differential between holding tank 56 and the chamber of the eye in which the fluid port is disposed, with the pressure differential being reduced by the total pressure loss of the aspiration flow along the aspiration path between the tank and port. In this mode, venting or reflux of the handpiece 110 may be accomplished by opening the solenoid vent valve 44, which pressurizes the holding tank 56 to increase the tank pressure and push fluid back towards (i.e., “vents”) the tubing and/or handpiece 110.

In some embodiments, the vent valve 44 may be used to increase the pressure inside the tank 56 to at or near atmospheric pressure. Alternatively, venting of the handpiece 110 may be accomplished in this mode by closing pinch valve 58, and by rotation peristaltic pump 54 in reverse (e.g., clockwise in FIG. 2A). Accordingly, aspiration network 50 allows system 100 to operate in either flow-based (e.g. peristaltic) and/or vacuum-based (e.g. venturi) pumping modes and to incorporate three different venting modes. In some embodiments, an additional valve is added that may be used to fluidly couple the irrigation line 51 to the aspiration flow network 50, thus providing an addition option for venting or refluxing the handpiece 110.

FIG. 2B illustrates another exemplary surgical cassette system in a functional block diagram that shows the components and interfaces that may be employed in accordance with an aspect of the present design.

The present design effectively splits the aspiration line from handpiece 110 into at least two separate fluid pathways where one is connected to collector 206 and the other to the air/fluid reservoir 204, which is also connected to collector 206. Splitting the fluid pathways in this way allows one line designated for vacuum regulated aspiration, venting, and/or reflux and the other line designated for peristaltic aspiration, venting, and/or reflux. However, the aspiration line, or the at least two separate fluid pathways may be connected with air/fluid reservoir 204. The vacuum regulated aspiration line 226 connects to reservoir 204, wherein fluid may be aspirated, vented, and/or refluxed to or from reservoir 204 through the line 226. The peristaltic line connects directly to the collector and aspirates, vents, and/or refluxes through the aspiration line 223, 225 without requiring a connection to reservoir 204.

Surgical cassette venting system 200 may include a fluid vacuum sensor 201, flow selector valve 202, reservoir 204, collector 206, and fluid pathways, such as interconnecting surgical tubing, as shown in FIG. 2B. The cassette arrangement 250 may include connections to facilitate easy attachment to and removal from the instrument host 102 as well as handpiece 110 and vacuum pump arrangement 207. The present design contemplates two or more pumps, where the surgical cassette arrangement may operate with fluid pathways or other appropriate fluid interconnections interfacing with the two or more pumps.

Cassette arrangement 250 is illustrated in FIG. 2B to simply show components that may be enclosed within the cassette. The size and shape of cassette 250 is not to scale nor accurately sized, and note that certain components, notably peristaltic pump 203, interface with the cassette but in actuality form part of the device which the cassette attaches to. Further, more or fewer components may be included in the cassette than are shown in FIGS. 2A and 2B depending on the circumstances and implementation of the cassette arrangement 250.

Referring to FIG. 2B, handpiece 110 is connected to the input side of fluid vacuum sensor 201, typically by fluid pathways such as fluid pathway 220. The output side of fluid vacuum sensor 201 is connected to flow selector valve 202 within cassette arrangement 250 via fluid pathway 221. The present design may configure flow selector valve 202 to interface between handpiece 110, balanced saline solution (BSS) fluid bottle 112, pump 203, which is shown as a peristaltic pump but may be another type of pump, and reservoir 204. In this configuration, the system may operate flow selector valve 202 to connect handpiece 110 with BSS fluid bottle 112, reservoir 204 or with pump 203 based on signals received from instrument host 102 resulting from the surgeon's input to GUI host 101.

The flow selector valve 202 illustrated in FIG. 2B provides a single input port and may connect port ‘0’ to one of three available ports numbered ‘1’, ‘2’, and ‘3’. The present design is not limited to one flow selector valve, and may be realized using two flow selector valves each having at least two output ports, possibly connected together to provide the functionality described herein. For example, a pair of two output port valves may be configured in a daisy chain arrangement, where the output port of a first valve is directly connected to the input port of a second valve. The instrument host may operate both valves together to provide three different flow configurations. For example, using two valves, valve one and valve two, valve one may use output port one, which is the supply for valve two. Valve two may connect to one of two ports providing two separate paths. When valve one connects its input port to its second output port rather than the output port that directs flow to the second valve, a third path is provided.

Thus while a single flow selector valve 202 is illustrated in FIG. 2B, it is to be understood that this illustration represents a flow selector valve arrangement, including one or more flow selector valves performing the functionality described herein, and is not limited to a single device or a single flow selector valve. It is also contemplated that flow selector valve 202 may be a pinch valve or multiple pinch valves as shown in FIG. 2A, and for example as shown in co-assigned U.S. patent application Ser. No. 11/937,456, the entirety of which is incorporated by reference herein. It is also contemplated that flow selector valve 202 and fluid vacuum sensor 201 may be a single unit, e.g. fluid vacuum sensor 201 may comprise or be a part of flow selector valve 202.

It is also envisioned that flow selector valve 202 may be or comprise one or more pinch valves. The one or more pinch valves may be located along fluid pathway 221 and/or 223, or any other fluid pathway as discussed herein. Further, there may be one or more fluid pathways couples with handpiece 110 and extending to various components of cassette arrangement 250, including a first fluid pathway from fluid vacuum sensor 201 to collector 206 via pump 203 and/or a second fluid pathway to reservoir 204. In another embodiment, fluid pathway 220 is a single fluid pathway that couples with fluid vacuum sensor 201. From fluid vacuum sensor 201, the single fluid pathway 220 may divide into two fluid pathways, one to collector 206 via pump 203 and one to reservoir 204. Further, one or more pinch valves and/or flow selector valve 202 may be located along the fluid pathway between fluid vacuum sensor 201 and collector 206 and/or between fluid vacuum sensor 201 and reservoir 204.

The present design's fluid vacuum sensor 201, for example a strain gauge or other suitable component, may communicate or signal information to instrument host 102 to provide the amount of vacuum sensed in the handpiece fluid pathway 220. Instrument host 102 may determine the actual amount of vacuum present based on the communicated information.

Fluid vacuum sensor 201 monitors vacuum in the line, and can be used to determine when flow should be reversed, such as encountering a certain pressure level (e.g. in the presence of an occlusion), and based on values obtained from the fluid vacuum sensor 201, the system may control selector valve 202 and the pumps illustrated or open the line to reflux from irrigation. It is to be understood that while components presented in FIG. 2 and other drawings of the present application are not shown connected to other system components, such as instrument host 102, but are in fact connected for the purpose of monitoring and control of the components illustrated. Flow selector valve 202 and fluid vacuum sensor 201 may also exist as a single unit.

With respect to fluid vacuum sensor 201, emergency conditions such as a dramatic drop or rise in pressure may result in a type of fail-safe operation. The present design employs fluid vacuum sensor 201 to monitor the vacuum conditions and provide signals representing vacuum conditions to the system such as via instrument host 102 for the purpose of controlling components shown including but not limited to flow selector valve 202 and the pumps shown. Alternative embodiments may include flow sensors (not shown).

Multiple aspiration and ventilation options are available in the design of FIG. 2B. In the arrangement where the selector valve 202 connects handpiece 110 with BSS bottle 112, the present design allows for venting of fluid from BSS bottle 112 to eye 114 as indicated by directional flow arrow ‘Z’ 236 and arrow ‘A’ 222 in FIG. 2B. In the arrangement where the flow selector valve 202 connects handpiece 110 with peristaltic pump 203, the present design may allow for aspiration from eye 114 directly to collector 206 as indicated by flow indicated in the directions of ‘X’ 238, arrow B 242, and arrow E at 232 as illustrated in FIG. 2B. Reversing direction of pump 203 can result in venting and/or refluxing.

In the arrangement where the cassette system flow selector valve 202 connects handpiece 110 with reservoir 204, the present design allows for aspiration from eye 114 directly to reservoir 204 as indicated by directional flow arrow ‘X’ 238, and arrow C 240 in FIG. 2B. Arrows/directions 238, 242, and 232 illustrate the flow of fluid for peristaltic pumping. Arrow 224 indicates the direction of operation for peristaltic pump 203 where fluid originating at handpiece 110 is pumped through line 223 toward line 225 during aspiration. Arrows/directions 238 and 240 illustrate the flow of fluid for venturi pumping.

Although venting is shown from BSS bottle 112, venting and/or irrigation is not represented in FIG. 2B via the pumps. However, the present design may allow for venting and/or reflux using the pumps associated with the cassette where the arrows in FIG. 2B are reversed; for example, indicating pump 203 is reversed or operates in a counter-clockwise direction. In this arrangement, the design may effectively split the aspiration line from the handpiece into two distinct lines, one arranged for peristaltic operation and the second line arranged for vacuum regulated operation via an air/fluid reservoir.

Reservoir 204 may contain air in section 211 and fluid in section 212. Surgical cassette system 200 may connect reservoir 204 with collector 206 using fluid pathways, such as surgical tubing or similar items. In this arrangement, pump 205 may operate in a clockwise direction in the direction of arrow 228 to remove fluid from the reservoir 204 through fluid pathway 227 and deliver the fluid to collector 206 using fluid pathway 229. The present design illustrates a peristaltic pump as pump 205, a component within instrument host 102, but other types of pumps may be employed. This configuration may enable the surgical cassette 200 to remove unwanted fluid and/or material from reservoir 204.

The fluid pathways or flow segments of surgical cassette system 200 may include the fluid connections, for example flexible tubing, between each component represented with solid lines in FIG. 2B.

Vacuum pump arrangement 207 is typically a component within instrument host 102, and may be connected with reservoir 204 via fluid pathway or flow segment 230. In the configuration shown, vacuum pump arrangement 207 includes a pump 208, such as a venturi pump and an optional pressure regulator 209 (and valve (not shown)), but other configurations are possible. In this arrangement, vacuum pump arrangement 207 may operate to remove air from the top of reservoir 204 and deliver the air to atmosphere (not shown). Removal of air from reservoir 204 in this manner may reduce the pressure within the reservoir, which reduces the pressure in the attached fluid pathway 226, to a level less than the pressure within eye 114. A lower reservoir pressure connected through flow selector valve 202 may cause fluid to move from the eye, thereby providing aspiration. The vacuum pump arrangement 207 and reservoir 204 can be used to control fluid flow into and out of reservoir 204. Vacuum pump arrangement 207 may also be used to vent the aspiration line to air by opening a valve to the venturi pump.

The optional pressure regulator 209 may operate to add air to the top of reservoir 204 which in turn increases pressure and may force the air-fluid boundary 213 to move downward. Adding air into reservoir 204 in this manner may increase the air pressure within the reservoir, which increases the pressure in the attached fluid aspiration line 226 to a level greater than the pressure within eye 114. A higher reservoir pressure connected through flow selector valve 203 may cause fluid to move toward eye 114, thereby providing venting or reflux.

An alternate method of creating positive pressure in reservoir 204 is running pump 205 in a counter-clockwise direction. Running pump 205 in a counter-clockwise direction will increase the amount of air in section 211 in reservoir 204.

It is to be noted that higher pressure in reservoir 204 causes more fluid flow and potentially more reflux from reservoir 204 to handpiece 110. If the lines from the reservoir 204 are plugged or otherwise occluded, providing pressure to reservoir 204 can result in venting and/or reflux. Venting in this context results in the release of pressure. Reflux occurs when a pump is reversed sending fluid in the opposite direction of normal flow (e.g. toward the eye). In a reflux condition, the surgeon can control the amount of fluid flowing back through the fluid pathways and components.

The present design may involve peristaltic operation, aspirating fluid from eye 114 to collector 206 illustrated in FIG. 2B, or venting fluid to the eye 114 to reduce the amount of pressure in the aspiration line (where such venting is only shown from BSS bottle 112 in FIG. 2). Peristaltic pumping is generally understood to those skilled in the art, and many current machines employ peristaltic and/or venturi pumps as the vacuum or pressure sources. Generally, a peristaltic pump has fluid flowing through a flexible tube and a circular rotor with a number of rollers attached to the periphery of the circular rotor. As the rotor turns, fluid is forced through the tube. Venturi pumping, or pressure or aspiration or aspirator pumping, produces the vacuum using the venturi effect by providing fluid through a narrowing tube. Because of the narrowing of the tube, the speed at which the fluid travels through the tube increases and the fluid pressure decreases (the “Venturi effect”). As may be appreciated, operating pumps in one direction or another can change the pressure and the operation of the associated device, such as the operation of the cassette in the present design.

FIG. 3 is a functional block diagram illustrating a surgical cassette system configured for venting using a balanced saline solution (BSS) bottle in accordance with an aspect of the present design.

In the arrangement where the flow selector valve 202 connects handpiece 110 with BSS bottle 112, the present design may allow for venting of fluid to eye 114 directly from BSS bottle 112 and/or the line between flow selector valve 202 and BSS bottle 112, where fluid from BSS bottle 112 and/or the line flows toward and through flow selector valve 202. The fluid flow continues to flow toward and through flow selector valve 202 in the direction indicated by arrow 321. In order to vent from BSS bottle 112, instrument host 102 may signal flow selector valve 202 to connect port ‘0’ to port ‘1’. When the flow selector valve 202 switches to position ‘1,’ fluid may flow from BSS bottle 112 and/or the line between BSS bottle 112 and flow selector valve 202 to handpiece 110 as indicated by directional arrows 322 and 321 as shown in FIG. 3. During fluid venting from bottle 112 and/or the line between BSS bottle 112 and flow selector valve 202, the present design may arrange the bottle position at an elevated height relative to the eye 114, thus realizing a positive pressure source.

FIG. 4 is a functional block diagram illustrating a surgical cassette system 400 configured for normal peristaltic aspiration. The present design may configure flow selector valve 202 to connect handpiece 110 to pump 203 and may operate selector valve 202 to connect fluid pathway 421 at port ‘0’ to fluid pathway 422 at port ‘3’ of flow selector valve 202. In this aspiration configuration, reservoir 204 is not employed. As pump 203 operates in a clockwise direction to pump fluid in the direction shown by arrow 424, the present design aspirates fluid from eye 114 to collector 206 following the path formed by connecting fluid pathway 420 from the handpiece to fluid vacuum sensor 201, continuing through fluid pathway 421 toward the flow selector valve 202 where a fluid line is connected from flow selector valve 202 to pump 203 and moving fluid in the direction shown by the arrow above fluid pathway 422. Clockwise pump operation shown by arrow 423 forces fluid into fluid pathway 425 in direction 424 toward collector 206. During an ocular procedure, the surgeon may stop the flow of fluid into the eye by stopping pump 203. When pump 203 is stopped, the rollers within the peristaltic pump stop moving and fluid through this path ceases to move or flow.

FIG. 5 illustrates a surgical cassette system 500 configured for venting and reflux operation. The present design may configure flow selector valve 202 to connect handpiece 110 to pump 203 from port ‘3’ to port ‘0’. As the pump 203 operates in a counter-clockwise direction as shown by arrow 523, the present design may vent fluid through fluid pathway 525 in direction of flow arrows at 524, 523, 522, and 521 and ultimately to fluid pathway 220. Note that in both FIGS. 4 and 5, flow selector valve 202 neither operates to take fluid from nor output fluid to reservoir 204.

In the configuration of FIG. 5, the system can stop the inflow of fluid from fluid pathway 525 to the eye by stopping pump 203 or closing flow selector valve 202, or both. The internal volume of fluid pathway 525 has sufficient fluid volume to provide venting and/or reflux.

The present design may alternately employ vacuum pump arrangement 207 to aspirate fluid from eye 114 to reservoir 204 as illustrated in FIG. 6, or applying pressure thus forcing fluid from reservoir 204 through selector valve 202 and irrigating eye 114 as illustrated in FIG. 7.

FIG. 6 is a functional block diagram illustrating the system configured for vacuum pump arrangement 207 aspiration operation where the present design may operate either in a normal venturi aspiration mode to create a vacuum at fluid pathway 626. Again, flow selector valve 202 connects handpiece 110 with reservoir 204 from port ‘2’ to port ‘0’. In this aspiration configuration, pump 203 is not in use and typically not operating. Vacuum pump arrangement 207 may operate to allow pressure to be removed from reservoir 204 either by venting to atmosphere or drawing a vacuum. Removing or reducing pressure using vacuum pump arrangement 207 may move air-fluid boundary 213 upward at 645 to aspirate fluid from eye 114 to reservoir 204. Again, vacuum pump arrangement 207 may include or be attached to a venturi pump or pumping device. The fluid path from eye 114 to reservoir 204 follows the direction indicated by the arrows above fluid passageway 621 and to the right of fluid passageway 626. Optionally, to vent and/or reflux, pressure regulator 209 may be used to increase the pressure in reservoir 204 to cause fluid to flow through fluid pathway 626 toward handpiece 110 via flow selector valve 202.

FIG. 7 is a functional block diagram illustrating a surgical cassette system 700 configured for venting and/or reflux operation in accordance with an aspect of the present invention. The present design may configure flow selector valve 202 to connect handpiece 110 with reservoir 204 from port ‘2’ to port ‘0’. Vacuum pump arrangement 207 may operate to provide pressure to reservoir 204 via pressure regulator 209. Applying or increasing pressure using pressure regular 209 of vacuum pump arrangement 207 may move air-fluid boundary 213 downward in the direction of 745 causing fluid to flow from reservoir 204 and/or fluid pathway 726 to eye 114.

In sum, the present design surgical cassette system provides for aspiration, venting, and/or reflux using pumping operations. A plurality of pumps are typically employed, including a first pump and a second pump, where a first pump may be pump 203, shown as a peristaltic pump in FIG. 2B, and pump 208, representing a venturi pump in certain embodiments shown herein.

The instrument host 102 may provide a signal to position or switch flow selector valve 202 for desired peristaltic or vacuum regulated operation. Aspiration, venting, and/or reflux may be controlled in various ways, including but not limited to switching offered to the surgeon on the instrument host 102, switching via a switch such as one provided on handpiece 110 or via a footswitch, or via automatic or semi-automatic operation, wherein pressure is sensed at some point, such as coming from the handpiece to the instrument host at sensor 201 or separately sensed by a sensor placed in the ocular region with pressure signals being provided to the instrument host 102. In general, automatic or semi-automatic operation entails sensing a drop or rise in pressure and either aspirating fluid to or venting fluid from the ocular region or eye 114. In any circumstance, the surgeon or other personnel are provided with the ability to run the pumps in any available direction, such as for cleaning purposes.

Other pumping states may be provided as discussed herein and based on the desires of personnel performing the surgical procedure. For example, in the case of the surgeon desiring aspiration operation as shown in FIG. 6 in all circumstances as opposed to aspiration as shown in FIG. 4, the surgeon may enable settings or the instrument host may provide for the surgeon to select such operation. Additionally, if the surgeon believes venturi pumping or vacuum regulator operation should be employed wherever possible, she may select that from the instrument host. Other configurations may be provided, including limiting ocular pressure within a desired range, and so forth.

Certain additional functionality or components may be provided in the current design. For example, a valve (not shown) may be located between pump 203 and flow selector valve 202 or between pump 203 and handpiece 112 in the design, such as in the design of FIG. 3, to build a bolus of fluid or build pressure between the valve and pump 203. Such a valve can thereby create positive pressure when pump 203, such as a peristaltic pump, reverses direction of flow and provides pressure to the valve. This positive pressure can be released by opening the valve thereby venting the system.

Referring to FIG. 1, the instrument host 102 will generally include at least one processor for processing instructions and sending command signals to other components of the system, and memory for storing instructions. The instrument host 102 and GUI host may be housed in a console. The instructions generally include methods for operating the system 100. Methods disclosed herein may be stored as instructions on the memory.

FIG. 8 shows a graph 802 which depicts a system switching from a first pump to a second pump according to one embodiment of the invention. The system may be the system 100 depicted in FIG. 1. Curve V_(I) shows the operation of the first pump in terms of aspiration level (which may be flow-rate or vacuum level) versus time T. The first pump may be a volumetric, e.g. peristaltic or other displacement, pump. The first pump is capable of attaining a limited aspiration level, as shown. Curve P_(I) shows the operation of the second pump in terms of aspiration level versus time T. The second pump may be a pressure, e.g. venturi or other pressure differential, pump and capable of a higher aspiration level than the first pump. As shown, through cassette arrangement 250, the second pump may begin operation while the first pump is operating at its maximum aspiration level, and thus a transitional time T_(R) between the peak aspiration levels is constantly increasing. Note that the time for initiating of a newly energized pump may occur before, during, or after a start time of the ramp-down or decreasing of aspiration flow from a previously operating pump. Similarly, a complete halt of flow or end of the ramp-down may occur before, during or after the end of the ramp-up, so that the transitions shown schematically herein are simplified. Also, the ramp-up and ramp-down of aspiration may more accurately be represented by curves (rather than single linear slopes). Nonetheless, the ramp-up of the newly employed pump (the second pump) will typically start before the ramp-down of the first pump has been completed. Thus, there is typically no time delay between switching of the pumps. Automatic switching between pumping systems, without the need for user interaction may be applied by automated control of the flow selector valve 202 or pinch valve 58. Switching may occur as a series of cycles or pulses, and thus occur over a very short period of time, in some examples having a frequency of a few milliseconds, less than a second, and/or a few seconds. A user may preprogram how and/or when switching between multiple pumps occurs. It also envisioned that the first pump may be a vacuum based pump (e.g. Venturi) and the second pump may be a flow based pump (e.g. peristaltic).

FIG. 9A shows a method 900 for applying aspiration to a probe, according to one embodiment of the invention. Method 900 may be employed on system 100 shown in FIG. 1. At operation 902 a first pump, operating at a first flow-rate (e.g. a low flow-rate), aspirates via a probe which is in a region of an eye. The probe for example may be a phacoemulsification device or a vitrectomy device. The first pump may be a volumetric, e.g. peristaltic, pump or a pressure pump, e.g. venturi. At operation 904 it is determined whether the probe is insufficiently occluded. To determine whether the probe is insufficiently occluded a flow and/or vacuum sensor may be used.

Phacoemulsification probes may optimally work with a sufficiently occluded aspiration port, as the ultrasound tip may then engage the target tissue. However, low aspiration rates are typically not strong enough to bring particles to the probe. Insufficient occlusion may be detected by sensing pressure or flow changes, or no changes within the aspiration channel. Examples of sensing occlusion through pressure differentials are shown in co-assigned U.S. patent application Ser. No. 11/461,741, which is incorporated by reference in its entirety.

If the probe is sufficiently occluded to operate as desired, then the method 900 returns to operation 902. If the probe is insufficiently occluded then the method 900 proceeds to operation 906. At operation 906 a command signal is generated to switch from the first pump to a second pump, which may be a pressure pump (e.g. venturi pump) or a volumetric pump (e.g. peristaltic). At operation 908 the second pump, operating at a second flow-flow rate (e.g. high flow-rate), aspirates via the probe which is in a region of the eye to help draw in cataract particles. At operation 910 it is determined whether the probe is insufficiently occluded. If the probe is insufficiently occluded, then the method 900 returns to operation 908. If the probe is sufficiently occluded, then a command signal is generated in operation 912 to switch from the second pump to the first pump, and the method 900 reverts to operation 902. According to an embodiment, a processor may be configured to, during pumping of aspiration flow along the aspiration pathway at the first pump rate and in response to insufficient occlusion of the aspiration pathway, generate a command signal so as to induce pumping of the aspiration flow along the aspiration pathway at the second pump rate. Further, the processor may be configured to provide a second command signal to energize the distal tip with ultrasound energy or increase the ultrasound energy at the distal tip during sufficient occlusion of the distal tip at the first pump rate. The second pump rate may be applied for a predetermined time in response to the second command signal. The second command signal may be generated in response to a change in flow rate and/or vacuum, e.g. in response to a pressure differential along the aspiration pathway being less than a threshold; or an increase or decrease in flow rate and/or vacuum. The threshold may be determined by the user or created a program default.

FIG. 9B shows a graphical depiction of the method 900 shown in FIG. 9A, according to one embodiment of the invention. The curve of pump 1 is shown at a normal operating aspiration rate in zone 914. An increase in aspiration rate (flow), shown in zone 916, indicates that the probe is insufficiently occluded. Accordingly, an automatic command signal is given to switch from the first pump to the second pump or run the first pump and the second pump simultaneously. It is also envisioned that the command signal to switch between multiple pumps may be controlled by the user. Zone 918 shows the second pump operating at a high flow aspiration rate. A decrease in the second pump aspiration rate or an increase in measured vacuum, shown in zone 920, indicates that the probe has been sufficiently occluded. In some embodiments the system may briefly switch back to the volumetric pump (or run simultaneously) to facilitate measurement of pressures so as to determine if the aspiration flow path is occluded as desired. A command signal (which may be automatic) is given to revert to the first pump, and a lower aspiration rate, as shown in zone 930. The time period in which second pump is operated may be very short, for example approximately 20 milliseconds (or less), less than a second, or less than 10 seconds. Phacoemulsification ultrasound energy may be applied while the second pump is in use, and/or when sufficient occlusion is detected.

FIG. 10A shows a method 1000 for applying aspiration to a probe according to one embodiment of the invention. Method 1000 may be employed on system 100 shown in FIG. 1. At operation 1010 ultrasonic energy is cycled on to a probe, along with a first pump operating a first flow-rate (e.g. low aspiration flow-rate). The probe for example may be a phacoemulsification device or a vitrectomy device. The first pump may be a volumetric, e.g. peristaltic, pump or a pressure pump, e.g. venturi at a low vacuum. At operation 1020 ultrasonic energy is cycled off, along with the first pump, and a second pump is cycled on, which operates at a second rate (e.g. high aspiration flow-rate) to draw in cataract particles to the probe while ultrasonic energy is not being applied. Additionally, the ultrasonic energy may be periodically applied at varying rates according to one or more predetermined duty cycles when the aspiration port is insufficiently occluded. Alternatively, a second pump may be cycled on, which operates at a high aspiration flow rate to draw in cataract particles to the probe based on a predetermined duty cycle, or a predetermined operation cycle (on/off of a pump). The second pump may be a pressure pump (e.g. venturi pump) or a volumetric pump (e.g. peristaltic). Method 1000 may continuously cycle between operations 1010 and 1020 for a predetermined amount of time, according to a predetermined duty cycle. Optionally, ultrasonic energy is not applied according to the predetermined duty cycle, if the probe is insufficiently occluded when the first pump is operating. The cycles shown may be pre-programmed or pre-selected by the user. For example the user may wish to cycle the first pump for 3 ms and the second pump for 10 ms. The cycles may also increase or decrease in time, for example pump 1 (3 ms)→pump 2 (10 ms)→pump 1 (20 ms)→pump 2 (70 ms)→etcetera. The cycles may be programmed by the user or chosen from a one or more stored cycles. Additionally, although the cycles show that the first pump shuts off, the first pump (or second) may be continuously on and the other pump pulsed on and off in cycles in an overlapping manner. According to an embodiment, ultrasonic energy may be applied at various and for varying intervals (e.g. duty cycle) and/or one or more pumps may be activated at various and for varying intervals in sync or out of sync with the ultrasonic energy. The intervals may vary in length of time, power level, and/or pump activation and the number of pumps activated.

FIG. 10B shows a graphical depiction of method 1000 as shown in FIG. 10A, according to one embodiment of the invention. Cycles 1030A show the operation of the first pump which are shown to be synchronized with ultrasonic energy operations 1050. Cycles 1040 show the operation of the second pump. The second pump operates when ultrasonic energy is not being applied. Curve 1030B shows the operation of a first pump being higher when the probe is not sufficiently occluded, with the system optionally detecting the insufficient occlusion based on pressure along the aspiration flow path during peristaltic pumping resulting in an automatically increased aspiration rate. Ultrasonic energy may optionally not be applied during curve 1030B. While schematically shown as a continuous ultrasonic energy 1050, the ultrasound may be pulsed during cycles 1030A. To detect and/or monitor whether there is an occlusion, flow sensors, vacuum sensors, differential pressures, etc. may be used.

As used herein, the first pump and the second pump may comprise a flow-based pump and/or a vacuum based pump, e.g. the first pump may comprise a vacuum based pump and the second pump may comprise a flow-based pump or vice versa or the first pump and the second pump may comprise the same type of pump.

FIG. 11A shows a method 1100 for applying aspiration to a probe, according to one embodiment of the invention. Method 1100 may be employed on system 100 shown in FIG. 1. In operation 1110 a low flow-rate aspiration level from a first pump is applied to a probe. The probe for example may be a phacoemulsification device or a vitrectomy device. The first pump may be a volumetric, e.g. peristaltic, pump. In operation 1120 it is determined whether the probe has been sufficiently occluded. If the probe is not sufficiently occluded the method 1100 may return to operation 1110 or alternatively switch to a high flow-rate aspiration level from a second pump and/or adjust the rate of the first pump. The second pump may be a pressure pump (e.g. venturi pump). If the probe is sufficiently occluded, then the method proceeds to operation 1130. At operation 1130 an alternating high-flow rate aspiration and reflux (or low aspiration) cycle may be automatically applied. The cycle may occur for a predetermined amount of time. The combination of a high flow-rate aspiration and reflux (or low aspiration) cycle may cause a pulverizing effect on cataract tissue, and effectively break up cataract tissue without the need for ultrasonic energy. However, ultrasonic energy may optionally be applied. The high flow-rate aspiration and reflux (or low aspiration) cycle may be applied by a second pump, for example, a venturi pump, the first or peristaltic pump, or both. Alternatively, switching between the low flow-rate aspiration level and the high flow-rate aspiration level may be implemented to achieve a transient induced effect to help break up cataract tissue.

FIG. 11B shows a graphical depiction of method 1100, as shown in FIG. 11A, according to one embodiment of the invention. Curves 1140 show the operation of the first pump applying a low flow-rate aspiration to the probe. Curves 1150 and 1160 show cyclical applications of high flow-rate aspiration and reflux, respectively, to the probe. Curves 1150 and 1160′ show cyclical applications of high and low flow rates. The cycles of curves 1150 and 1160 may be operated according to a predetermined duty cycle, and may include more cycles than what is shown.

FIG. 12 shows a method 1200 for applying aspiration to a probe, according to one embodiment of the invention. Method 1200 may be employed on system 100 shown in FIG. 1. At operation 1210 a first pump, operating at a low flow-rate, aspirates a probe which is in a region of an eye. The probe for example may be a phacoemulsification device or a vitrectomy device. The first pump may be a volumetric, e.g. peristaltic, pump. At operation 1220 the system 100 receives a user input, which may be for example through foot pedal 104, to switch to high flow-rate aspiration from a second pump. The second pump may be a pressure pump (e.g. venturi pump) or a high rate peristaltic pump. At operation 1230 the system responds to the user input from operation 1220 and aspirates the eye with a high flow-rate aspiration from the second pump. At operation 1240 the system receives a user input, which may be for example through foot pedal 104, to switch back to the low flow-rate aspiration from the first pump, and accordingly cycles back to operation 1210. The foot pedal 104 may operate through longitudinal and latitudinal movement (pitch and yaw, respectively), for example the first pump may be activated through longitudinal movement and the second pump through latitudinal movement, or vice-versa. Alternatively, longitudinal movement may alter aspiration flow levels, while latitudinal movement switches between pumps. Control of various parameters, such as, but not limited to aspiration rate, pump rate, pump type, ultrasonic power level, and adjustments thereof may be programmed to any movement or switch of the foot pedal and/or may be combined such that movement in one direction controls multiple parameters. Exemplary dual linear foot pedals may be seen in U.S. Pat. Nos. 6,674,030; 6,452,123; and 5,268,624, the full disclosures of which are incorporated herein by reference.

According to an embodiment, a system may comprise a first pump and a second pump, wherein the first pump is a flow based pump and the second pump is a vacuum based pump. During a procedure a surgeon may use the first pump to aspirate irrigation fluid and/or material from the eye and upon detection of an occlusion, the second pump is turned on or increased. Turning on the second pump or increasing the vacuum level of the second pump allows the occlusion to be held against the distal end of the tip of the handpiece. Without being limited to a particular theory, holding the occlusion tightly to the distal end of the tip of the handpiece may assist with breaking up of lens material (occlusion) and provide more user control over the lens material.

The methods and devices disclosed herein may also be used with co-assigned and concurrently filed U.S. Provisional Patent Application No. 61/198,626, entitled AUTOMATICALLY SWITCHING DIFFERENT ASPIRATION LEVELS AND/OR PUMPS TO AN OCULAR PROBE, which is incorporated by reference herein in its entirety.

It should be noted that the examples disclosed herein may describe low-flow rate pumps as peristaltic pumps, and high flow-rate pumps as venturi pumps. These are merely examples and are not limiting to the embodiments disclosed herein, for example high-flow rate peristaltic pumps may be used in lieu of high flow-rate venturi pumps, and low flow-rate venturi pumps may be used in lieu of low-flow rate pumps peristaltic pumps. Additionally, a low flow-rate venturi pump may be used in conjunction with a high flow-rate venturi pump, and a low flow-rate peristaltic pump may be used in conjunction with a high flow-rate peristaltic pump.

As will be understood by those skilled in the art, the present invention may be embodied in other specific forms without departing from the essential characteristics thereof. Those skilled in the art will recognize, or be able to ascertain using no more than routine experimentation, many equivalents to the specific embodiments of the invention described herein. Such equivalents are intended to be encompassed by the following claims. 

What is claimed is:
 1. A system for removing tissue from within an eye, comprising: a probe having a distal tip insertable into the eye, the distal tip having an aspiration p ort and a distal end; and a console coupled with the aspiration port along an aspiration pathway, wherein the console comprises a processor and a pump system, wherein the pump system comprises a first pump for providing a first pump rate and a second pump for providing a second pump rate that is higher than the first pump rate; and wherein the processor is configured to, during pumping of aspiration flow along the aspiration pathway at the first pump rate and in response to insufficient occlusion of the aspiration pathway, generate a first command signal to induce pumping of the aspiration flow along the aspiration pathway at the second pump rate by activating the second pump and deactivating the first pump, and during pumping of aspiration flow along the aspiration pathway at the second pump rate and in response to sufficient occlusion of the aspiration pathway, generate a second command signal to induce pumping of the aspiration flow along the aspiration pathway at the first pump rate by activating the first pump and deactivating the second pump.
 2. The system of claim 1, wherein the processor is further configured to provide a third command signal to energize the distal tip with ultrasound energy during sufficient occlusion of the distal tip at the first pump rate, wherein the second pump rate is applied for a predetermined time in response to the third command signal, and wherein the third command signal is generated in response to a pressure differential along the aspiration pathway being less than a threshold.
 3. The system of claim 1, wherein the processor is further configured to provide a third command signal to energize the distal tip with ultrasound energy during sufficient occlusion of the distal tip at the first pump rate, wherein the second pump rate is applied for a predetermined time in response to the third command signal, and wherein the third command signal is generated in response to a change in flow rate and/or vacuum.
 4. The system of claim 1, wherein the processor is further configured to provide a third command signal to increase ultrasound energy at the distal tip during sufficient occlusion of the distal tip at the first pump rate, wherein the second pump rate is applied for a predetermined time in response to the third command signal, and wherein the third command signal is generated in response to a change in flow rate and/or vacuum.
 5. The system of claim 1, wherein the processor is further configured to provide a third command signal to increase ultrasound energy at the distal tip during sufficient occlusion of the distal tip at the first pump rate, wherein the second pump rate is applied for a predetermined time in response to the third command signal, and wherein the third command signal is generated in response to a pressure differential along the aspiration pathway being less than a threshold.
 6. The system of claim 1, wherein the first pump is a peristaltic pump and the second pump is a venturi pump.
 7. The system of claim 1, wherein the first pump is deactivated after the second pump is activated.
 8. The system of claim 1, wherein the first pump is deactivated after the second pump rate is higher than the first pump rate.
 9. A method for removing tissue from within an eye, comprising: activating a first pump for providing a first pump rate; pumping aspiration flow along an aspiration pathway at the first pump rate; detecting an occlusion of the aspiration pathway; generating a first command signal to induce pumping of the aspiration flow along the aspiration pathway at a second pump rate which is higher than the first pump rate, the second pump rate provided by activating a second pump and deactivating the first pump, wherein the first command signal is generated upon detection of an insufficient occlusion; and holding the occlusion against a distal end of a distal tip of a probe insertable into the eye during operation of the second pump; and generating a second command signal to induce pumping of the aspiration flow along the aspiration pathway at the first pump rate by activating the first pump and deactivating the second pump, wherein the second command signal is generated upon detection of a sufficient occlusion. 